Device and method for locally resolved control of a radiation dose

ABSTRACT

A device for locally resolved control of a radiation dose (ρ (γ,e+) ({right arrow over (r)})) applied with a pulsed particle beam ( 6 ) in particle beam therapy, with a processing unit ( 24 ), which is set up to detect continuously a count rate of x-ray quanta ( 14 ) measured with a positron emission tomograph ( 2 ) and to determine the applied radiation dose (ρρ (γ,e+) ({right arrow over (r)})) from the pattern of the measured count rate, by determining by computation from the measured pattern of the count rate the time intervals (I n ), in which an interaction of the particle beam ( 6 ) takes place at the application site and by rejecting these time intervals (I n ) for the determination of the applied radiation dose (ρ (γ,e+) ({right arrow over (r)})).

The invention relates to a device and method for locally resolved control of a radiation dose applied with a pulsed particle beam in particle beam therapy.

In particle beam therapy a tumor in a patient is irradiated with protons or ions in a pulsed manner. This pulsed proton or ion radiation is supplied in this context by a particle accelerator, for example a synchrotron. Radiation pulse sequences, having an infinite number of radiation pulses, alternate here with beam delays. The radiation parameters here are set in such a manner that the greatest degree of destruction possible of the tumor tissue is achieved with the smallest possible degree of damage to the surrounding healthy body tissue. They are determined before the radiation therapy takes place. In order to be able to control the radiation dose applied at the application site or, respectively, at the site of the tumor, the applied radiation dose is determined in a locally resolved manner using a positron emission tomograph. This makes use of the fact that positron emitters are formed at the application site by nuclear conversions during the radiation process. Every positron emitter releases a positron as it decays, said positron together with an electron annihilating with an energy of 511 keV respectively in two x-ray quanta. These x-ray quanta are measured by the positron emission tomograph. An evaluation algorithm is used to determine the respective site of origin of the x-ray quanta from this location information. The radiation dose applied at the application site is calculated in a locally resolved manner by temporally integrating decay events in the radiation period. It is thus possible to verify, in a locally resolved manner, the extent to which the radiation dose actually applied differs from the planned radiation dose. It is thus possible to adapt the radiation parameters for further radiation processes.

The positron emission tomograph has a processing unit, in which two tests are carried out, to establish whether two detected x-ray quanta can be traced back to a positron decay. On the one hand it is verified whether the two x-ray quanta lie in a narrow time window, what is known as a coincidence window, of around 2-10 ns duration. In a second test it is verified whether the x-ray quanta respectively have an energy of 511 keV. Since the accuracy of the energy measurement is limited, x-ray quanta, which originate from am energy window of around 350 keV to 650 keV, are assigned to a positron decay.

A problem arises during the evaluation of the measured x-ray quanta. During the interaction of the particle beam at the application site the energy input due to the protons or ions causes further numerous nuclear reactions to be induced, which similarly result in the emission of x-ray quanta. If two such x-ray quanta lie in a common coincidence window, positron decays are simulated. Therefore the positron emission tomograph is not generally used for measurement purposes during the interaction of the pulsed particle beam with the body tissue. Measuring only takes place in the beam delays between the radiation pulse sequences. Since these beam delays only make up around 30 to 70% of the total beam exposure time, compared with the radiation pulse sequences, also referred to as beam extraction phases, and since positron decays are not taken into account during the beam extraction phases, measuring using positron emission tomographs is subject to relatively major error. This error is perpetuated in the calculation of the radiation dose applied in a site-dependent manner.

Generation of x-ray quanta, which are not attributable to a positron decay, takes place almost exclusively during the interaction of a radiation pulse with the body tissue. The radioactive isotopes occurring in the body tissue in addition to the positron beams are so short-lived that their decay takes place during or immediately after such a radiation pulse. A precise temporal identification of the time intervals, in which the radiation pulses interact with the tumor tissue, would also make it possible to evaluate the coincidence events, which occur in the time intervals between radiation pulses. This would allow a decisive improvement in the evaluation statistics.

The radiation pulse sequence is known, since the particle accelerator receives a corresponding control signal, generated by a control unit, but the protons or ions first cover a free flight distance from the site of origin or reference site in the particle accelerator to the application site, in other words to the tumor to be irradiated, followed by a path inside the body. Since the decay of the radioactive isotopes also takes a specific time, it is not clear from the x-ray quanta measured as a function of time, at which time exactly the interaction of a radiation pulse with the body tissue takes place.

In P. Crespo et. al., “Suppression of Random Coincidences During In-Beam PET Measurements at Ion Beam Radiotherapy Facilities”, IEEE Transactions on Nuclear Science, Vol. 52, 2005, page 980 ff two methods are proposed for determining the times of the radiation pulses and therefore the times of the delays between the radiation pulses.

With the first method an additional detector in the beam path is used to measure when a radiation pulse occurs. Since the additional detector is disposed close to the application site, there is only a small time offset between the detector site and the application site. Very precise synchronization is required here between the measurement signals measured by the positron emission tomograph and the measurement signals of the additional detector. This requires a complex electronic unit.

With the second measuring method the control signals, with which the particle accelerator is triggered by way of the control unit, are evaluated. The radiation pulse sequence is therefore known. An electrical component, what is known as a phase trigger, is used to determine the delay between the reference site and the application site. This method also requires very complex and precise synchronization between the control signal of the particle accelerator and the positron emission tomograph.

With both methods described those time intervals are determined, in which an interaction takes place with the particle beam at the application site. Those coincidence events, the recording time of which lies in such an interval, are then rejected, in other words not used for an evaluation. Determination of the time intervals is however very complex in both instances.

The object of the invention is to allow a locally resolved detection of the applied radiation dose in a simple and economical manner.

According to the invention this object is achieved by the feature combination in claim 1.

The inventive device comprises a processing unit, which is used to register x-ray quanta measured using a positron emission tomograph as a function of time, location and energy. The time intervals, during which an interaction of the particle beam takes place at the application site, are first determined from this count rate. A coincidence unit is also used to determine which of the x-ray quanta lie in a narrow time window, what is known as a coincidence window, and represent what are known as coincidence events. In general a beam-induced positron concentration is measured with the aid of the positron emission tomograph.

Those coincidence events, which were measured temporally in one of the determined time intervals, are then rejected for the determination of the applied radiation dose. The applied radiation dose is then calculated from the remaining coincidence events. This is a purely software-based solution, which determines the radiation pulse sequence based on the count rate of x-ray quanta that is measured in any case. Such a solution can be implemented in a simple and economical manner. Complex calibration operations, as required with a hardware-based solution, do not have to be implemented here. Nor is there any need for a complex additional technical measuring arrangement.

The processing unit is preferably set up to evaluate the beam delays between the individual radiation pulse sequences to control the applied radiation dose. Since the time intervals between the individual beam pulses are also evaluated, the evaluation is carried out over almost the entire radiation period. This results in a clear improvement in respect of the count statistics. The measurement error, to which the determination of the locally resolved, applied radiation dose is subject, is significantly reduced compared with the former procedure, in which only the beam delay periods were evaluated.

In one development the processing unit is set up to determine a time offset of the radiation pulse sequence at the application site in relation to the time of its generation. This time is predetermined for example by a control unit, which generates a control signal to generate the radiation pulse sequence. The temporal pattern of the radiation pulse sequence is known. The corresponding information is forwarded from the control unit to the processing unit. The processing unit computes this radiation pulse sequence with the temporal pattern of the count rate of characteristic decay events, which are measured as characteristic detector events. Those decay events, which occur either only or particularly frequently during the interaction of a radiation pulse with the body tissue, are selected here from the sum of all the decay events measured using the detectors of the positron emission tomograph.

The time offset of the radiation pulse sequences at the application site gives the time intervals, at which the individual radiation pulses interact with the tumor tissue and in which many further x-ray quanta are generated in addition to x-ray quanta from positron decay. Coincidence events, which are measured in these time periods, are not used for the evaluation.

The processing unit is preferably set up here to determine the time offset, by simulating the radiation pulse sequence at the time of its generation by means of a periodic function. This function is computed with the temporal pattern of the count rate of the characteristic decay events. This gives the time offset. Simulation of the radiation pulse sequence by a periodic function is very simple to implement. In the simplest instance it is a rectangular function, having a constant value during the period of a radiation pulse and being otherwise zero.

In an expedient variant the processing unit is set up to determine the time offset by forming a mathematical correlation function from the periodic function and the temporal pattern of the count rate of the characteristic decay events, said mathematical correlation function for example having the appearance of a convolution integral. The time offset of the radiation pulse sequence at the application site compared with the time of its generation is then clear from the maximum of the correlation function. The formation of a correlation function is a method known anyway in mathematics, which is easy to convert for programming purposes. It is thus possible to determine the time offset in a particularly simple manner.

Individual decay events are for example suitable for the selection of the characteristic decay events characterizing the interaction of a radiation pulse with the body tissue. In this context the temporal patterns of individual decay events are preferably analyzed, their energy significantly exceeding the energy of an x-ray quantum generated from the decay of a positron. This ensures that x-ray quanta generated during positron decay are not used inadvertently for the evaluation. This would be possible for example, if only one of the two x-ray quanta was detected by a detector, while the second x-ray quantum was absorbed by body tissue.

Suitable characteristic decay events are also decay events comprising two or three x-ray quanta in one coincidence window. In this process both real coincidences during the decay of a positron are detected as well as random coincidences, when for example a single x-ray quantum and an x-ray quantum resulting from a positron decay are detected together in the coincidence window.

All these decay events described have in common the fact that they occur with particular frequency during the interaction of a radiation pulse with the body tissue. By forming a correlation function with the periodic function, it is possible to determine the time offset of the radiation pulse at the application site reliably from the temporal pattern of the count rate of said characteristic decay events, where there is sufficient radiation intensity. The extraction of said characteristic decay events from the totality of all decay events detected by the processing unit is achieved in a simple manner using a sorting algorithm. Information about the temporal pattern of characteristic decay events is thus easy to access. To improve the evaluation it is also possible to consider the count rates of different groups of said characteristic decay events in combination.

In one development the processing unit uses all the characteristic events in a specific energy window to determine the offset time. This energy window can be adjusted by programming in such a manner that the correlation function shows a clear maximum. This allows the offset time to be determined in a reliable manner. The single adjustment of the energy window during a commissioning phase is simple and uncomplicated to implement.

According to the invention the object is also achieved by a method as claimed in claim 11. Further advantageous embodiments will emerge from the subclaims dealing with a method. The advantages and preferred embodiments specified in respect of the device should be applied appropriately thereto.

An exemplary embodiment of the invention is described in more detail below with reference to a drawing, in which:

FIG. 1 shows a schematic diagram of a device for particle beam therapy with a positron emission tomograph for locally resolved control of an applied radiation dose,

FIG. 2 shows a time-intensity diagram of a particle beam with two radiation pulse sequences and a beam delay therebetween,

FIG. 3 shows a schematic diagram of an evaluation system for the locally resolved determination of the applied radiation dose,

FIG. 4 shows a schematic diagram of an evaluation algorithm to determine the time intervals, in which radiation pulses occur at the application site,

FIG. 5 shows a periodic rectangular function,

FIG. 6 shows the temporal pattern of a count rate of characteristic decay events,

FIG. 7 shows a correlation function formed from the functions illustrated in FIG. 5 and FIG. 6, and

FIG. 8 shows a list of those time intervals of a beam pulse sequence, in which an interaction of the particle beam takes place at the application site.

FIG. 1 shows a schematic diagram of a device for particle beam therapy, having a positron emission tomograph 2 for locally resolved control of an applied radiation dose. For particle beam therapy a particle accelerator 4 generates a pulsed particle beam 6. This pulsed particle beam 6 contains protons or ions. Its pulse sequence is predetermined by a control unit 8. The pulsed particle beam 6 is used to irradiate tumor tissue 12 in a person 10 in a specific manner. Radiation causes positron emitters to form at the application site, in other words within the tumor tissue 12 and these decay very quickly, emitting a positron in each instance. Each of these positrons annihilates with an electron of an adjacent atom, in that two x-ray quanta 14 fly out from the annihilation site in opposing directions, in other words at a 180° angle. The two x-ray quanta 14 are registered respectively by one of the detectors 18 disposed in a circle round the application site and held by a holding device 16. Two measurement signals are generated in this process, which are verified by means of two measuring lines 20 first for their coincidence, in other words their quasi-simultaneity, in a coincidence unit 22. All decay events are also registered in a processing unit 24 by ways of the measuring lines 20. The data is stored in a data storage unit there, with the energy of each x-ray quantum 14, its time of registration and the registering detector 18 being detected. The registering detector 18 holds the location information of the x-ray quantum 14.

In the processing unit 24 position decay events are assigned to the x-ray quanta 14 measured in coincidence. The location information of the detectors 18 thus allows conclusions to be drawn about the decay site in the tumor tissue 12. The applied radiation dose is calculated in a locally resolved manner by means of integration over the radiation period. The calculated radiation dose is compared with the radiation dose predetermined by the control unit 8 in the context of the radiation therapy schedule. This comparison serves to control the particle beam therapy and allows adjustment of future radiation sessions.

FIG. 2 shows the intensity pattern of the pulses particle beam 6 as a function of time. It shows two pulse sequences X_(n) and X_(n+1), between which there is a beam delay R. The continuous index n here runs from 1 to a maximum value Nag. Thus a total of N_(max) radiation pulse sequences are considered. Both radiation pulse sequences have a start point t_(n,start) and/or t_(n+1,start) and an end point t_(n,end) and/or t_(n+1,end). The radiation pulse sequence X_(n) comprises a total of four radiation pulses with a pulse length of Δt and a period of T_(n). The radiation pulse sequence X_(n+1) comprises six radiation pulses with a pulse length of Δt and a period of T_(n+1). In practice radiation pulse sequences and beam delays alternate over the entire period of irradiation of the tumor tissue 12. Radiation pulse sequences typically have a duration of around 1 to 10 seconds and beam delays a duration of 1 to 3 seconds. The individual radiation pulses typically have from 1 to 1,000 particles and a length of around 10 to 100 ns. The period length T_(n) and thus the time difference between two adjacent radiation pulses is several 100 ns. In practice a radiation pulse sequence comprises significantly more than four or six radiation pulses. FIG. 2 is simply an idealized illustration.

FIG. 3 shows how the locally resolved determination of the applied radiation dose takes place. The detectors 18 of the positron emission tomograph 2 detect decay occurring in a narrowly dimensioned time window of several ns, known as coincidence events, by means of the coincidence unit 22. The formula

P(γ_(i),γ_(j))=P(γ_(i)({right arrow over (r)} _(i) ,t _(i) ,E _(i)),γ_(j)({right arrow over (r)} _(j) ,t _(j) ,E _(j)), i≠j

shows that these coincidence events contain location, time and energy information for two different (i≠j) x-ray quanta γ_(i), γ_(j).

The detectors 18 also detect all the x-ray quanta γ_(k)({right arrow over (r)}_(k),t_(k),E_(k)) with their location, time and energy information.

Characteristic decay events S(t,E) are selected from among these x-ray quanta γ_(k). These are x-ray quanta 14 with an energy significantly exceeding the energy for a positron decay of 511 keV. The count rate of these characteristic decay events S(t,E) is considered in respect of its time-dependent pattern.

Characteristic decay events, which comprise two or three x-ray quanta in one coincidence window, can however also be evaluated by way of example. Groups of characteristic decay events S(t,E) can also be considered in a common manner.

The control unit 8 of the particle accelerator 4 transmits information by way of a measuring line 20 to the processing unit 24 regarding the period T_(n) and pulse duration Δt used to generate control signals for a radiation pulse sequence X_(n).

The characteristic decay events S(t,E) and radiation pulse sequences X_(n) are used to determine, by way of a method still to be described, those time intervals I_(n), at which an interaction of the corresponding radiation pulses takes place at the application site, in the tumor tissue 12.

The only coincidence events P(γ_(i),γ_(j)) considered further are those whose two x-ray quanta have an energy between 350 keV and 650 keV:

P(γ_(i),γ_(j))=P(γ_(i)({right arrow over (r)} _(i) ,t _(i) ,E _(u)),γ_(j)({right arrow over (r)} _(j) ,t _(j) ,E _(j))) ∀E_(i),E_(j)ε[350 keV,650 keV].

Since the x-ray quanta lose energy in the body tissue, at the time of registration their energy is less than the energy value of 511 keV characteristic of a positron decay at the site of origin of the two x-ray quanta.

These coincidence events are sought out from the totality of all coincidence events in the processing unit 24 by means of a sorting algorithm.

Of the coincidence events P(γ_(i),γ_(j)) those, for which at least one of the two registered times t_(i) and t_(j) lies in one of the intervals I_(n), are rejected. This leaves the events

${{\overset{\sim}{P}\left( {\gamma_{1},\gamma_{j}} \right)} = {{P\left( {{\gamma_{i}\left( {\overset{\rightarrow}{r},t_{i},E_{i}} \right)},{\gamma_{j}\left( {{\overset{\rightarrow}{r}}_{j},t_{j},E_{j}} \right)}} \right)}\mspace{14mu} {\forall t_{i}}}},{t_{j} \notin {\bigcup\limits_{n = 1}^{N_{\max}}{{I_{n}(t)}.}}}$

From the remaining coincidences {tilde over (P)}(γ_(i),γ_(j)) the radiation dose ρ^((γ,e+))({right arrow over (r)}) applied over the radiation period is determined in a locally resolved manner by integration over the entire radiation time:

${\rho^{({\gamma,{e +}})}\left( \overset{\rightarrow}{r} \right)} = {{{K\left( {e +} \right)} \cdot {\int_{t_{start}}^{t\; {end}}{\Sigma \left( {\overset{\sim}{P}\left( {\gamma_{1},\gamma_{2}} \right)} \right)}}}_{\overset{\_}{r}}{\cdot {t}}}$

Here Σ({tilde over (P)}(γ₁,γ₂))|_({right arrow over (r)}) designates the totality of all registered positron decays at the site {right arrow over (r)}, K(e+) a factor specifying the radiation dose resulting from a single positron decay {tilde over (P)}(γ_(i),γ_(j)), t_(start) the start and t_(end) the end of the radiation process.

The indexing (γ,e+) shows that the x-ray quanta are from a positron decay.

Since the radiation pulses only make up a very short time period in relation to the radiation time, the coincidence events {tilde over (P)}(γ_(i),γ_(j)) constitute almost [lacuna] occurring coincidence events. This results in very precise measurement of the radiation dose ρ^((γ,e+))({right arrow over (r)}) applied in a locally resolved manner.

FIG. 4 shows the algorithm for determining those intervals, in which the radiation pulses interact with the tumor tissue 12. The continuous index n again identifies the individual radiation pulse sequences. These radiation pulse sequences are considered in order from the first (n=1) to the last (n=N_(max)). The information relating to the respective period T_(n) of the M(n) radiation pulses within the radiation pulse sequence X_(n) and the radiation pulse duration Δt is simulated with the aid of a periodic function F_(n)(t). Here

F _(n)(t)=F _(n)(t+mT _(n)) ∀m=1, . . . , M(n),

in other words the periodic function F_(n)(t) has the period T_(n). This gives a series of a total of M(n) identical segments of the function F_(n)(t) on the time axis.

Such a periodic function F_(n)(t) is shown in FIG. 5. This is a step function, which assumes the value 1 for the time, during which a radiation pulse is emitted, and is otherwise zero, as set out in the formal equation

${F_{n}(t)} = \left\{ {\begin{matrix} 1 & {if} & {{t \in \left\lbrack {{mT}_{n},{{mT}_{n} + {\Delta \; t}}} \right\rbrack},{m = 0},\ldots \mspace{11mu},{M(n)}} \\ 0 & {otherwise} & \; \end{matrix}.} \right.$

Generally the periodic function F_(n)(t) is computed with the time-dependent count rate of characteristic events S(t,E) by way of a convolution. The resulting convolution K_(n)(z) is determined over the period from the start t_(n,start) to the end t_(n,end) of the radiation pulse sequence:

K_(n)(z) = ∫_(t_(n, start))^(t_(n, end))S(t) ⋅ F_(n)(t − z)t

The convolution K_(n)(z) then accurately provides a clear maximum φ_(n), when the count rate of the characteristic decay events S(t,E) correlates with the periodic function F_(n)(t).

This situation is shown by way of example in FIG. 7. An evaluation of the maximum in the convolution space provides the time offset φ_(n).

The temporal displacement of the radiation pulses at the application site compared with the reference site results from this time offset φ_(n).

FIG. 8 shows the actual time intervals I_(n) determined from a complete radiation pulse sequence X_(n) for the interaction of the radiation pulses with the tumor tissue 12. For each individual radiation-pulse of the total M(n) of radiation pulses an interval of pulse length Δt results with

I _(n) ^((m)) =[m·T _(n)+φ_(n) ,m·T _(n)+φ_(n) +Δt] ∀m=0, . . . , M(n)−1.

The interval I_(n) is obtained by combining all M(n) intervals I_(n) ^((m)) to give

$I_{n} = {\bigcup\limits_{m = 0}^{{M{(n)}} - 1}\left\lbrack {{{m \cdot T_{n}} + \phi_{n}},{{m \cdot T_{n}} + \phi_{n} + {\Delta \; t}}} \right\rbrack}$

This sequence of time intervals I_(n) is determined for every radiation pulse sequence X_(n).

The mathematical combination

$\bigcup\limits_{n = 1}^{N_{\max}}{I_{n}(t)}$

of all N_(max) time intervals designates all the time segments, which are not to be used for the evaluation. Coincidence events P(γ_(i),γ_(j)), which lie in one of these intervals I_(n), are not used to determine the radiation dose ρ^((γ,e+))({right arrow over (r)}) applied in a locally resolved manner over the treatment period. 

1. A device for locally resolved control of a radiation dose (ρ^((γ,e+))({right arrow over (r)})) applied with a pulsed particle beam (6) in particle beam therapy, comprising a processing unit (24), which is set up to detect continuously a count rate of x-ray quanta (14) measured with a positron emission tomograph (2) and to determine the applied radiation dose (ρ^((γ,e+))({right arrow over (r)})) from the pattern of the measured count rate, by determining by computation from the measured pattern of the count rate the time intervals (I_(n)), in which an interaction of the particle beam (6) takes place at the application site and by rejecting these time intervals (I_(n)) for the determination of the applied radiation dose (ρ^((γ,e+))({right arrow over (r)})).
 2. The device as claimed in claim 1, with the processing unit (24) being set up to evaluate beam delays (R_(n)) between the individual radiation pulse sequences (X_(n)) to control the applied radiation dose (ρ^((γ,e+))({right arrow over (r)})).
 3. The device as claimed in claim 1 or 2, with the processing unit (24) being set up to determine a time offset (φ_(n)) of the radiation pulse sequence (X_(n)) at the application site in relation to the time of its generation, by [lacuna] the time information relating to the generation of the radiation pulse sequence (X_(n)) with the temporal pattern of characteristic decay events (S(t,E)).
 4. The device as claimed in claim 3, with the processing unit (24) being set up to determine the time offset (φ_(n)), by simulating the time information relating to the generation of the radiation pulse sequence (X_(n)) mathematically by means of a periodic function (F_(n)) and computing this function with the temporal pattern of the characteristic decay events (S(t,E))
 5. The device as claimed in claim 4, with the processing unit (24) being set up to determine the time offset (φ_(n)), by forming a mathematical correlation function (K_(n)) from the periodic function (F_(n)) and the characteristic decay events (S(t,E)), with the time offset (φ_(n)) being clear from the maximum of the correlation function (K_(n)).
 6. The device as claimed in claim 4 or 5, with the processing unit (24) being set up to process a rectangular function as the periodic function (F_(n)).
 7. The device as claimed in one of claims 4 to 6, with the processing unit (24) being set up to process characteristic decay events (S(t,E)), which are individual decay events.
 8. The device as claimed in one of claims 4 to 7, with the processing unit (24) being set up to process characteristic decay events (S(t,E)), which have an energy, significantly exceeding the energy of an x-ray quantum generated by the decay of a positron.
 9. The device as claimed in one of claims 4 to 8, with the processing unit (24) being set up to process characteristic decay events (S(t,E)), which comprise two or three x-ray quanta.
 10. The device as claimed in one of claims 4 to 9, with the processing unit (24) being set up to adjust an energy window predetermined for the determination of the time offset (φ_(n)), in such a manner that the time offset (φ_(n)) can be determined in a reliable manner.
 11. A method for locally resolved control of a radiation dose applied with a pulsed particle beam (6) in particle beam therapy, wherein a count rate of x-ray quanta is detected continuously with the aid of a positron emission tomograph (2) and wherein the applied radiation dose (ρ^((γ,e+))({right arrow over (r)})) is determined from the pattern of the count rate, by first determining by computation the time intervals (I_(n)), in which an interaction of the particle beam (6) takes place at the application site and by rejecting these time intervals (I_(n)) for the determination of the site-dependent radiation dose (ρ^((γ,e+))({right arrow over (r)})).
 12. The method as claimed in claim 11, with the beam delays (R_(n)) between the individual radiation pulse sequences (X_(n)) being evaluated to control the applied radiation dose (ρ^((γ,e+))({right arrow over (r)})).
 13. The method as claimed in claim 11 or 12, with a time offset (φ_(n)) of the radiation pulse sequence (X_(n)) being determined at the application site in relation to a reference site, by computing the radiation pulse sequence (X_(n)) at the reference site with the temporal pattern of characteristic decay events (S(t,E)).
 14. The method as claimed in claim 13, with the time offset (φ_(n)) being determined by simulating the radiation pulse sequence (X_(n)) at the site of origin mathematically by means of a periodic function (F_(n)) and by computing said function with the temporal pattern of characteristic decay events (S(t,E)).
 15. The method as claimed in claim 14, with the time offset (φ_(n)) being determined by forming a mathematical correlation function (K_(n)) from the periodic function (F_(n)) and the characteristic decay events (S(t,E)), with the time offset (φ_(n)) being clear from the maximum of the correlation function (K_(n)).
 16. The method as claimed in claim 14 or 15, with the periodic function (F_(n)) being a rectangular function.
 17. The method as claimed in one of claims 14 to 16, with the characteristic decay events (S(t,E)) being individual decay events.
 18. The method as claimed in one of claims 14 to 17, with the characteristic decay events (S(t,E)) having an energy significantly exceeding the energy of an x-ray quantum generated by the decay of a positron.
 19. The method as claimed in one of claims 14 to 18, with the characteristic decay events (S(t,E)) comprising two or three x-ray quanta, which lie in a predetermined time window.
 20. The method as claimed in one of claims 14 to 19, with an energy window predetermined for the determination of the time offset (φ_(n)) being adjusted in such a manner that the time offset (φ_(n)) can be determined in a reliable manner. 